I. Introduction
IN most current positron emission tomography (PET) detector designs, based on small scintillation crystals coupled to position-sensitive photomultiplier tubes, sensitivity is lost due to the dead space between the crystals. Furthermore, the spatial resolution may be limited by inter-crystal scatter and parallax errors. Monolithic scintillation detectors, consisting of several cm3 of scintillating material coupled to one or more avalanche photodiode (APD) arrays, can avoid these problems. The entry point of an incoming annihilation photon on the detector front surface is derived from the distribution of the scintillation light on the APD arrays. This readout method, which does require a-priori knowledge of the incidence angle, intrinsically provides depth of interaction (DOI) information. Previous work has shown that detectors consisting of a LYSO crystal coupled to two APD arrays have a good spatial resolution, with very little degradation for angles of incidence up to 30° [1].